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WO2012014739A1 - Dispositif de diagnostic ultrasonore - Google Patents

Dispositif de diagnostic ultrasonore Download PDF

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Publication number
WO2012014739A1
WO2012014739A1 PCT/JP2011/066406 JP2011066406W WO2012014739A1 WO 2012014739 A1 WO2012014739 A1 WO 2012014739A1 JP 2011066406 W JP2011066406 W JP 2011066406W WO 2012014739 A1 WO2012014739 A1 WO 2012014739A1
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WIPO (PCT)
Prior art keywords
elastic
image
unit
elasticity
dimensional
Prior art date
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Ceased
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PCT/JP2011/066406
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English (en)
Japanese (ja)
Inventor
慎介 猪上
哲矢 林
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Hitachi Healthcare Manufacturing Ltd
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Hitachi Medical Corp
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Filing date
Publication date
Application filed by Hitachi Medical Corp filed Critical Hitachi Medical Corp
Priority to EP11812330.6A priority Critical patent/EP2599445A1/fr
Priority to JP2012526442A priority patent/JP5770189B2/ja
Priority to US13/809,700 priority patent/US9101289B2/en
Priority to CN201180027580.8A priority patent/CN102933155B/zh
Publication of WO2012014739A1 publication Critical patent/WO2012014739A1/fr
Anticipated expiration legal-status Critical
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/08—Clinical applications
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/48—Diagnostic techniques
    • A61B8/483—Diagnostic techniques involving the acquisition of a 3D volume of data
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/46—Ultrasonic, sonic or infrasonic diagnostic devices with special arrangements for interfacing with the operator or the patient
    • A61B8/461—Displaying means of special interest
    • A61B8/466—Displaying means of special interest adapted to display 3D data
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/48—Diagnostic techniques
    • A61B8/485—Diagnostic techniques involving measuring strain or elastic properties

Definitions

  • the present invention relates to an ultrasonic diagnostic apparatus that displays an ultrasonic image of a diagnostic region in a subject using ultrasonic waves, and particularly to an ultrasonic diagnosis that displays an elastic image such as strain or elastic modulus as a three-dimensional elastic image. Relates to the device.
  • the ultrasonic diagnostic apparatus measures the ultrasonic reflectance of a living tissue in a subject using ultrasonic waves, generates a reflectance tomographic image of a diagnostic site obtained by converting the ultrasonic reflectance into luminance, and displays the image.
  • various ultrasonic images have been proposed that contribute to diagnosis by displaying images. For example, some tomographic tomographic images in a subject are acquired at intervals and tomographic volume data is constructed, and a three-dimensional tomographic image is constructed and displayed based on the multiple tomographic tomographic images. Proposed. According to this three-dimensional tomographic image, a living tissue can be grasped in three dimensions.
  • a technique has been proposed in which, for example, a blood vessel is designated as a continuum by specifying a blood vessel in a three-dimensional tomographic image (for example, Patent Document 1).
  • the average value of the voxel values of the region of interest set in the tomographic volume data is obtained, and adjacent voxels within the set range of voxel values within the set range are determined based on the upper and lower limits of the input voxel values.
  • the correlation between a pair of gray-scale tomographic image data taken for the same part is taken, the amount of movement of the living tissue, for example, the displacement is spatially differentiated to measure the strain, or the pressure change is applied to the living tissue as a histological diagnosis
  • An elastic modulus is measured, and an elastic image such as strain or elastic modulus is generated and displayed.
  • Elastic images are displayed by adding red, blue, and other hue information according to the amount of strain and elastic modulus of the living tissue.
  • By displaying mainly the hard part of the living tissue it is easy to spread the tumor. And size can be diagnosed (for example, Patent Document 3).
  • elastic values such as strain or elastic modulus are obtained at spatially continuous tomographic positions, elastic volume data is constructed, and 3D elastic images are constructed based on this. It has also been suggested to display.
  • the elastic image it was originally aimed at grasping a hard part such as a tumor, and in a three-dimensional elastic image, grasping the position and spread of the hard part of a hard part like a tumor. Is the aim.
  • a tissue such as a tumor generally displays a three-dimensional elastic image included in a surrounding soft tissue, there is a problem that a hard part is hidden by a soft part and is difficult to see.
  • the superficial portion is hardened by the pressing force for displacing the subject tissue, and a portion other than the desired portion may be displayed hard, and it is difficult to grasp the desired hard portion at a glance.
  • the problem to be solved by the present invention is to provide an ultrasonic diagnostic apparatus capable of displaying a three-dimensional elastic image of a lump of biological tissue having a set elasticity value.
  • the ultrasonic diagnostic apparatus of the present invention that solves the above problems includes a storage unit that stores elastic volume data generated based on ultrasonic image data acquired by transmitting and receiving ultrasonic waves to a subject, and the elasticity
  • An input unit that sets a region of interest in a space occupied by volume data, and an extraction unit that extracts a voxel group having a voxel value within a set elastic range set based on the elasticity value of the voxel of the region of interest from the elastic volume data
  • a three-dimensional elastic image creation unit for generating a three-dimensional elastic image by volume rendering the elastic volume data of the voxel group extracted by the extracting unit or the elastic volume data excluding the voxel group, and the three-dimensional elastic image
  • An image display unit that displays a three-dimensional elasticity image generated by the creation unit is included.
  • the voxel group included in the set elastic range set based on the elasticity value of the voxel included in the set region of interest is extracted, and based on the elastic volume data of the extracted voxel group Since the three-dimensional elasticity image is generated, a lump of living tissue having elasticity equivalent to that of the region of interest can be displayed as a three-dimensional elasticity image. That is, if the elasticity value of the voxel in front of the line of sight is not included in the set elastic range than the desired lump of living tissue, it is removed from the extracted voxel group, so that the 3D elasticity image can be displayed easily.
  • the set elastic range can be set based on an upper limit value and a lower limit value that are set separately, based on an average value of elastic values of a plurality of voxels included in the region of interest.
  • the present invention it is possible to generate a three-dimensional elastic image by volume rendering the elastic volume data excluding the extracted voxel group. For example, if a region of interest is set for a lump of biological tissue in front of the line of sight, the voxel group included in the set elastic range based on the lump is removed. As a result, it is possible to display a three-dimensional elastic image of the biological tissue located behind the removed voxel group in the line-of-sight direction.
  • a voxel group may be extracted not only for a lump of living tissue having elasticity intended by the examiner but also for a lump of living tissue at a distant position.
  • a lump of body tissue appears in the three-dimensional elastic image.
  • the image display unit displays a three-section elastic image in three orthogonal cross sections, and on the at least one image of the displayed three-section elastic image, the input unit
  • the region of interest can be set from That is, a cross-sectional image generation unit that generates a three-section elastic image of the elastic volume data in three orthogonal cross sections set by the input unit and displays the image on the image display unit, and the input unit displays the image on the image display unit.
  • the region of interest is input and set on the three-section elastic image.
  • the three-dimensional elasticity image and the three-section elasticity image are preferably color elasticity images in which the color tone is converted according to the elasticity value of the pixel.
  • the cross-sectional image generation unit generates an extracted 3-cross-section elastic image in the three orthogonal cross-sections of the elastic volume data of the voxel group extracted by the extraction unit or the elastic volume data excluding the voxel group, and the previous three-section elastic image Can be combined and displayed on the image display unit. According to this, the elasticity value of a desired body tissue lump can be observed with each synthesized cross-sectional elasticity image. Differences in the elasticity value of each part are more easily observed in the cross-sectional elasticity image than in the three-dimensional elasticity image of a lump of biological tissue.
  • the input unit of the present invention can form the region of interest set on the three-section elastic image displayed on the image display unit so that the region of interest can be expanded or reduced.
  • the extraction unit re-extracts the voxel group for the expanded or reduced region of interest
  • the 3D elastic image creation unit generates a 3D elastic image for the re-extracted voxel group.
  • the extraction unit extracts a voxel group included in each region of interest
  • the three-dimensional elasticity image creation unit is configured to extract the voxels extracted by the extraction unit. It is possible to generate a three-dimensional elastic image by volume rendering the elastic volume data of the group or the elastic volume data excluding the voxel group, and display it on the image display unit.
  • the extraction unit can extract, as a voxel group, voxels continuously connected to the center coordinates of each region of interest and the voxels located at the center coordinates.
  • the three-dimensional elasticity image may be generated with reduced opacity. it can.
  • volume editing that hides the voxel group in the range that is pushed in by pushing the volume end face using the input unit for 3D images. As a result, an unnecessary volume can be deleted or a cross section inside the volume can be observed.
  • volume editing can be performed only on the elastic volume data of the voxel group extracted by the extraction unit.
  • volume editing may be performed only on the elastic volume data excluding the extracted voxel group.
  • Block diagram of an ultrasonic diagnostic apparatus The figure explaining the example of an image display of Example 1 which concerns on construction
  • FIG. 6 is a diagram for explaining an image display example of a modification of the fifth embodiment.
  • FIG. 1 is a block configuration diagram of an embodiment of the ultrasonic diagnostic apparatus of the present invention, which is characterized by a method for generating a three-dimensional elastic image.
  • the ultrasonic diagnostic apparatus includes an ultrasonic probe 2 that is used in contact with the subject 1, and an ultrasonic probe 2 that is repeatedly applied to the subject 1 via the ultrasonic probe 2 at time intervals.
  • a transmission unit 3 that transmits sound waves, a reception unit 4 that receives time-series reflected echo signals generated from the subject 1, a transmission / reception control unit 5 that performs control to switch between transmission and reception of the transmission unit 3 and the reception unit 4, and A phasing addition unit 6 is provided for phasing and adding the reflected echo signals received by the reception unit 4 to generate RF signal frame data.
  • the transmission unit 3, the reception unit 4, the transmission / reception control unit 5, and the phasing addition unit 6 form a transmission / reception unit.
  • the tomographic image forming unit 7 that forms a two-dimensional tomographic image and the two-dimensional tomographic image formed by the tomographic image forming unit 7 are stored together with the acquisition position.
  • Tomographic volume data that generates tomographic volume data by performing three-dimensional coordinate conversion based on the two-dimensional tomographic image storage unit 35, the two-dimensional tomographic image stored in the two-dimensional tomographic image storage unit, and the acquisition position of the two-dimensional tomographic image
  • a two-dimensional elasticity image is constructed from the tomographic multi-frame construction unit 46 for creating a black and white tomographic image and the elasticity value of strain or elastic modulus calculated by the elasticity information computation unit 32
  • the ultrasound probe 2 is formed by arranging a plurality of transducers, and has a function of electronically performing beam scanning and transmitting / receiving ultrasound to the subject 1 via the transducers. .
  • the ultrasonic probe 2 is composed of a plurality of rectangular or fan-shaped transducers, mechanically swinging the transducers in a direction perpendicular to the arrangement direction of the plurality of transducers, and transmitting ultrasonic waves in three dimensions. Can be sent and received.
  • the ultrasonic probe 2 may be one in which a plurality of transducers are two-dimensionally arranged so that transmission / reception of ultrasonic waves can be electronically controlled.
  • the ultrasound probe 2 scans the ultrasound transmission / reception surface (scanning surface) in the minor axis direction, that is, in the direction orthogonal to the major axis direction in which a plurality of transducers are arranged, and It is only necessary to be able to measure a reflected echo signal of a volume within a predetermined range, and to be able to measure the scanning angle ⁇ of the ultrasonic beam on the scanning surface and the deflection angle ⁇ of the ultrasonic beam in the minor axis direction.
  • the ultrasonic probe 2 is configured to scan the ultrasonic beam on the scanning surface by the transmission / reception unit while receiving the reflected echo signal from the subject 1 while changing the deflection angle ⁇ .
  • the transmission unit 3 generates a transmission pulse for driving the transducer of the ultrasonic probe 2 to generate ultrasonic waves.
  • the transmission unit 3 has a function of setting a convergence point of transmitted ultrasonic waves to a certain depth.
  • the receiving unit 4 amplifies the reflected echo signal received by the ultrasonic probe 2 with a predetermined gain to generate an RF signal, that is, a received signal.
  • the ultrasonic transmission / reception control unit 5 is for controlling the transmission unit 3 and the reception unit 4.
  • the phasing and adding unit 6 receives the RF signal amplified by the receiving unit 4 and performs phase control, forms an ultrasonic wave reception beam at one or more convergence points, and generates an RF signal frame that is tomographic image data Data is generated.
  • the tomographic image construction unit 7 constructs a tomographic image of the subject, for example, a black and white tomographic image, based on the RF signal frame data from the phasing addition unit 6. That is, the tomographic image construction unit 7 inputs the RF signal frame data output from the phasing addition unit 6 based on the setting conditions of the image system control unit 44, and performs gain correction, log compression, detection, contour enhancement, filter Signal processing such as processing is performed to form a two-dimensional tomographic image. Further, an elastic information calculation unit 32 that obtains an elastic value such as strain or elastic modulus from the displacement information measured by the displacement measuring unit 30, and an elastic image configuration that constitutes a color elastic image from the elastic value calculated by the elastic information calculation unit 32 Part 34 is provided. The color elasticity image formed by the elasticity image construction unit 34 is stored in the two-dimensional elasticity image storage unit 39.
  • the elasticity image data stored in the two-dimensional elasticity image storage unit 39 or the image data generated based on the elasticity image data is converted by the switching synthesis unit 12 so as to match the display of the image display 13. ing.
  • an image system control unit 44 composed of a CPU that controls the components of the ultrasonic diagnostic apparatus in FIG. 1 and an interface unit 43 that gives instructions to the image system control unit 44 are installed.
  • the examiner variably controls the hue of the elastic image, the region of interest (ROI), the frame rate, and the like.
  • the pressure measuring unit 49 measures the pressure applied to the living tissue of the subject 1 when measuring the elasticity value.
  • a well-known method can be applied as a method of applying pressure to the living tissue.
  • a method of pushing and pulling the ultrasonic transmission / reception surface of the ultrasonic probe 2 with respect to the subject 1 or an object through the ultrasonic probe 2 can be applied.
  • a method of applying a drop impact of a weight to the specimen 1 a method of applying pressure by a mechanical or liquid balloon, a method of applying an impact of an ultrasonic pulse with a high sound pressure, or a body motion such as the pulsation of the subject 1 itself.
  • the method is known.
  • the pressure measurement method in the pressure measurement unit 49 is adopted in accordance with the selection of the method for applying these forces.
  • the RF signal frame data selection unit 28 selects a pair of RF signal frame data from a plurality of RF signal data from the phasing addition unit 6 stored in the RF signal frame data storage unit 27.
  • the RF signal frame data storage unit 27 sequentially secures RF signal data generated based on the time series, that is, the image frame rate, from the phasing addition unit 6 in the frame memory, and receives a command from the image system control unit 44.
  • N, M, and X are index numbers assigned to the RF signal frame data, and are natural numbers.
  • the displacement measuring unit 30 obtains the displacement of the living tissue from one set of RF signal frame data. For example, the displacement measurement unit 30 performs one-dimensional or two-dimensional correlation processing from a set of RF signal frame data (N) and RF signal frame data (X) selected by the RF signal frame data selection unit 28, and generates a tomogram. A one-dimensional or two-dimensional displacement distribution related to the displacement and movement vector corresponding to each point of the image, that is, the direction and magnitude of the displacement is obtained. Here, a block matching method is used to detect the movement vector.
  • the block matching method divides an image into blocks consisting of N ⁇ N pixels, for example, focuses on the block in the region of interest, searches the previous frame for the block that most closely matches the block of interest, and refers to this
  • predictive coding that is, processing for determining the sample value by the difference.
  • the strain data is calculated by spatially differentiating the movement amount of the living tissue, for example, the displacement.
  • the elastic modulus of the biological tissues corresponding to each point of the tomographic image is determined from the Young's modulus Y m, it is possible to obtain a two-dimensional elastic image data continuously.
  • the Young's modulus is a ratio of a simple tensile stress applied to the object and a strain generated in parallel to the tension.
  • the elastic image construction unit 34 is configured to include a frame memory and an image processing unit, and secures the elastic frame data output in time series from the elastic information calculation unit 32 in the frame memory, and stores the secured frame data.
  • the image processing unit performs image processing.
  • the elastic image is converted into three primary colors of light, that is, red (R), green (G), and blue (B) based on the elastic frame data, and is displayed on the image display 13 as a color image. For example, elastic data having a large strain is converted into a red code, and simultaneously elastic data having a small strain is converted into a blue code.
  • the gradation of red (R), green (G), and blue (B) has 256 levels, 255 means display at the maximum luminance, and conversely 0 means no display at all.
  • the ultrasound probe 2 can measure the transmission / reception direction ( ⁇ , ⁇ ) simultaneously with transmission / reception of ultrasonic waves, and the tomographic volume data creation unit 36 transmits / receives corresponding to the acquisition position of the two-dimensional tomographic image. Based on the direction ( ⁇ , ⁇ ), three-dimensional conversion is performed on a plurality of two-dimensional tomographic images to generate tomographic volume data.
  • the tomographic volume rendering unit 38 performs volume rendering using the following equations (1) to (3) that form a three-dimensional tomographic image from the tomographic volume data.
  • a (i) BOpacity [C (i)]-(3)
  • C (i) is the luminance value of the i-th voxel existing on the line of sight when a 3D tomographic image is viewed from a certain point on the created 2D projection plane.
  • Cout (i) is an output pixel value.
  • Cout (i-1) indicates the integrated value up to the i-1th.
  • a (i) is the opacity of the i-th luminance value existing on the line of sight, and is a tomographic opacity table (fault opacity table) taking values from 0 to 1.0 as shown in (3) above. .
  • the tomographic opacity table determines the contribution rate on the output two-dimensional projection plane (three-dimensional tomographic image) by referring to the opacity from the luminance value.
  • S (i) is a weight component for shading calculated from the luminance C (i) and the gradient obtained from the surrounding pixel values.
  • the normal of the surface centered on the light source and voxel i is the same. In this case, 1.0 is given for the strongest reflection, and 0.0 is given when the light source and the normal line are orthogonal to each other.
  • Aout (i) is integrated and converges to 1.0 each time it passes through the voxel. Therefore, as shown in (1) above, when the integrated value Aout (i-1) of the opacity up to the (i-1) th is about 1.0, the luminance value C (i) after the ith is output. Not reflected in the image.
  • the tomographic multi-frame configuration unit 46 constructs a cross-sectional tomographic image of a cross-sectional position arbitrarily set from the tomographic volume data.
  • the cross-sectional position can be arbitrarily set by the operator using the interface unit 43, and the set cross-sectional position is output to the tomographic multi-frame configuration unit 46 through the image system control unit 44.
  • a plurality of cross-sectional positions can be set, and the tomographic multi-frame configuration unit 46 outputs a plurality of cross-sectional tomographic images for a plurality of cross-sectional positions.
  • the displacement measuring unit 30 measures the displacement of the living tissue from a set of RF signal frame data selected by the RF signal frame data selecting unit 28 from a plurality of RF signal frame data stored in the RF signal frame data storage unit 27. . Then, the elasticity information calculation unit 32 calculates an elasticity value based on the measured displacement, and the elasticity image configuration unit 34 configures two-dimensional elasticity image data based on the elasticity value obtained from the elasticity information calculation unit 32.
  • any elastic information such as strain, elastic modulus, displacement, viscosity, and strain ratio can be applied to the elastic value.
  • the RF signal frame data is obtained spatially continuously in a direction orthogonal to the direction of arrangement of the plurality of transducers, so that an elastic image is also obtained accordingly. It is done.
  • a two-dimensional elasticity image storage unit 39 stores the two-dimensional elasticity image obtained spatially continuously and its acquisition position. Based on the two-dimensional elasticity image stored in the two-dimensional elasticity image storage unit 39 and the transmission / reception direction ( ⁇ , ⁇ ) corresponding to the acquisition position, the elasticity volume data creation unit 40 Conversion is performed to generate elastic volume data.
  • the elastic volume rendering unit 42 performs volume rendering on the elastic volume data using the following equations (4) to (6) to create a three-dimensional elastic image.
  • E (i) is the i-th elasticity value on the line of sight when a three-dimensional elasticity image is viewed from a certain point on the created two-dimensional projection plane.
  • Eout (i) is an output pixel value.
  • Eout (i-1) indicates the integrated value up to the (i-1) th.
  • a (i) is the opacity of the i-th elastic value existing on the line of sight, and is the elastic opacity shown in Expression (6) set in advance as a table.
  • S (i) is a weight component for shading calculated from the elastic value E (i) and the gradient obtained from the surrounding elastic values.
  • the normal of the surface centered on the light source and voxel i matches. In this case, 1.0 is given for the strongest reflection, and 0.0 is given when the light source and the normal line are orthogonal to each other.
  • Eout (i) and Aout (i) both have 0 as an initial value, and Aout (i) is integrated and converges to 1.0 each time it passes through a voxel as shown in Equation (5). Therefore, as shown in Equation (4), when the integrated value Aout (i-1) of the opacity of the i-1th voxel is about 1.0, the i-th and subsequent voxel values E (i) Is not reflected in the output image.
  • the elastic multi-frame configuration unit 48 cuts out a cross-sectional elasticity image corresponding to the set cross section of three orthogonal cross sections input and set by the inspector from the interface unit 43 from the elastic volume data, and constructs a cross-sectional elastic image in the set cross section.
  • the cross-sectional position set from the interface unit 43 is output to the elastic multi-frame configuration unit 48 through the image system control unit 44. Note that a plurality of cross-sectional positions can be set, and the elastic multi-frame configuration unit 48 outputs a plurality of elastic tomographic images for a plurality of cross-sectional positions.
  • the switching composition unit 12 includes a frame memory, an image processing unit, and an image selection unit.
  • the frame memory includes a three-dimensional tomographic image from the tomographic volume rendering unit 38, a cross-sectional tomographic image from the tomographic multi-frame configuration unit 46, a three-dimensional elastic image from the elastic volume rendering unit 42, and an elastic multi-frame configuration unit.
  • the cross section elasticity image from 48 is stored.
  • the image processing unit adds the three-dimensional tomographic image and the three-dimensional elastic image secured in the frame memory, or the cross-sectional tomographic image and the cross-sectional elastic image at a set ratio in accordance with a command from the image system control unit 44. Are synthesized.
  • the luminance information and hue information of each pixel of the composite image is obtained by adding each information of the black and white tomographic image and the color elastic image at a set ratio.
  • the image selection unit displays the 3D tomographic image and the 3D elastic image in the frame memory, or the cross sectional tomographic image and the cross sectional elastic image and the composite image data of the image processing unit on the image display unit 13.
  • the image to be selected is selected in accordance with a command from the image system control unit 44. Note that the tomographic image and the elastic image may be displayed separately without being combined.
  • the detailed configuration of the selection coordinate calculation unit 51, the selection elasticity value calculation unit 52, and the selection volume calculation unit 53, which are features of the ultrasonic diagnostic apparatus of the present invention, and the construction procedure of the three-dimensional elasticity image will be described in the first to the following examples. This will be explained based on 7.
  • a color bar having a different color tone according to the elastic value is displayed in the display area of the three-dimensional elastic image. Is displayed. That is, the three-dimensional elasticity image and the three-section elasticity image are color elasticity images in which the color tone is converted according to the elasticity value of the pixel.
  • FIG. 2 shows an example of the display image of the first embodiment.
  • four images are displayed side by side.
  • the lower right image is a three-dimensional elastic image
  • the other images are three cross-sectional elastic images (elastic MPR) in three orthogonal cross sections (YZ, ZX, YX).
  • the illustrated example is an example of elastic volume data in which a soft volume 101 includes a prismatic hard volume 102 and a spherical hard volume 103 as shown in a three-dimensional elastic image.
  • the volume means a lump of living tissue.
  • the prismatic hard volume 102 and the spherical hard volume 103 are set to have the same hardness.
  • the elastic volume data is represented by XYZ coordinates of three orthogonal axes.
  • the operator sets the region of interest 104 on the arbitrary elastic MPR image 106 displayed on the image display 13 via the interface unit 43.
  • the selected coordinate calculation unit 51 calculates the center coordinates of the circular region of interest 104 set by the interface unit 43 using the coordinates on the elastic MPR image 105, for example.
  • the selected elasticity value calculation unit 52 outputs the range from (ms ⁇ vs) to (ms + vs) as the set elasticity range.
  • the set elastic range may be calculated using a statistical feature value other than the average value and the variance value of the elastic value in the region of interest, for example, the maximum value or the minimum value.
  • the selected volume calculation unit 53 first calculates the elasticity value included in (ms + vs) from the set elasticity range (ms-vs) output from the selection elasticity value calculation unit 52 in the elastic volume data.
  • the elastic volume data 107 possessed is extracted as a voxel group. Further, only the voxel group of the elastic volume data including the center coordinate position (i, j, k) output from the selected coordinate calculation unit 51 is extracted from the extracted elastic volume data 107.
  • the prismatic hard volume 102 is extracted as an extraction elastic volume.
  • the present embodiment is not limited to the above-described example, and the volume rendering is performed on the elastic volume data excluding the volume (voxel group) from which the voxel in the set elastic range determined by the set region of interest is extracted, and is three-dimensionally rendered.
  • Elastic images can be generated and displayed. In this way, for example, if the region of interest is set to the obstacle volume in front of the line of sight, the 3D elastic image from which the obstacle volume is removed is displayed, so that the work efficiency of the examiner is improved. There is.
  • the present embodiment is not limited to the three-dimensional elasticity image, but adapts the volume coordinates extracted by the selected volume calculation unit 53 to the tomographic volume data, and only the tomographic volume data corresponding to the extracted elastic volume data is obtained. It can also be extracted and rendered to display 3D tomographic images.
  • the storage unit storing the elastic volume data generated based on the ultrasonic image data acquired by transmitting and receiving ultrasonic waves to the subject, and the space occupied by the elastic volume data are concerned.
  • An input unit for setting a region an extraction unit for extracting a voxel group having a voxel value within a set elastic range set based on the elasticity value of the voxel of the region of interest, and a voxel extracted by the extraction unit 3D elasticity image creation unit that generates 3D elasticity image by volume rendering of elastic volume data of group or elasticity volume data excluding voxel group, and 3D elasticity image generated by 3D elasticity image creation unit
  • the image display part which comprises.
  • the extraction unit extracts the voxels that are continuously connected to the center coordinates of the region of interest and the voxels located at the center coordinates to form a voxel group.
  • the cross-sectional image generation unit that generates the three-section elastic image of the elastic volume data in the three orthogonal cross sections set by the input unit and displays the image on the image display unit, the input unit displays the image The region of interest is input and set in one of the three-section elastic images displayed on the screen.
  • the cross-sectional image generation unit generates the extracted three-section elastic image in three orthogonal cross sections of the elastic volume data excluding the voxel group or the elastic volume data extracted by the extraction unit, and the three cross-sections The image is combined with the elastic image and displayed on the image display unit.
  • the second embodiment is a method in which the selected elastic value calculating unit 52 uses an input value from the outside for calculating the set elastic range. For example, only the average elasticity value of the region of interest 104 in FIG. 2 is calculated, and the operator inputs the upper and lower limit values Ls corresponding to “ ⁇ vs” in the first embodiment using the interface unit 43 and sets the elastic range.
  • This is an embodiment that makes it possible to variably set. According to this, since the spread of the elastic value can be freely adjusted by the set elastic range of ms ⁇ Ls, it is possible to observe a three-dimensional elastic image of a part having a specific hardness.
  • FIG. 4 shows an example of the display image of the third embodiment.
  • the region of interest 108 is set and the extracted three-dimensional elasticity image 109 is displayed according to the first embodiment.
  • the elastic volume data creation unit 40 outputs the coordinate information of the extracted volume to the elastic multi-frame configuration unit 48.
  • the elastic multi-frame configuration unit 48 outputs the extracted cross-sectional image of the volume as the extraction region 110 in addition to the elastic MPR image of the first embodiment.
  • the switching composition unit 12 superimposes the extraction region 110 on the elastic MPR image of the first embodiment.
  • the superimposed display method may display only the outline of the extracted cross-sectional image of the volume, or may display only the extracted volume in a different color.
  • only the extraction area 110 may be displayed by deleting the elastic MPR image of the first embodiment.
  • FIG. 5 shows an example of the display image of the fourth embodiment.
  • the elastic volume 112 extracted in the set elastic range connected to the set region of interest is extracted, and on the elastic MPR image when the third embodiment is applied.
  • the extraction area 113 is displayed in FIG.
  • the elastic volume corresponding to the image 114 on the elastic MPR image is not included in the set elastic range of the set region of interest and may not be displayed.
  • a voxel included in the set elastic range is added, and the expanded extraction volume 116 is displayed. It goes without saying that not only the expansion but also the extraction area can be reduced.
  • the input unit is formed so as to be able to expand or reduce the region of interest set on the three-section elastic image displayed on the image display unit, and the extraction unit is configured to expand or reduce the region of interest.
  • a voxel group is re-extracted with respect to the three-dimensional elastic image creating unit, and a three-dimensional elastic image is generated with respect to the re-extracted voxel group.
  • FIG. 6 shows an example of the display image of the fifth embodiment. As shown in FIG. 6A, this is an example in which two regions of interest 119 and region of interest 120 are set on the elastic MPR image 118 from the interface unit 43.
  • the selected coordinate calculation unit 51 calculates the center coordinates of the region of interest 119 and the region of interest 120, respectively.
  • the center coordinate of the region of interest 119 is A (i, j, k), and the center coordinate of the region of interest 120 is B (s, t, u).
  • the selected elasticity value calculation unit 52 calculates a set elasticity range for each of the region of interest 119 and the region of interest 120.
  • the set elastic range of the region of interest 119 is A (s) to A (s '), and the set elastic range of the region of interest 120 is B (s) to B (s').
  • the selected volume calculation unit 53 extracts a volume corresponding to each of the region of interest 119 and the region of interest 120. That is, as shown in FIG. 6 (b), an extracted elastic volume having an elastic value included in the set elastic range A (s) to A (s') and including the center coordinate position A (i, j, k). 121 and an extracted elastic volume 122 having an elastic value included in the set elastic range B (s) to B (s ′) and including the center coordinate position B (s, t, u) are extracted and displayed.
  • the extraction unit extracts a voxel group included in each region of interest, and the 3D elastic image creation unit is extracted by the extraction unit.
  • Volume rendering is performed on the elastic volume data of the voxel group or the elastic volume data excluding the voxel group to generate a three-dimensional elastic image, which is displayed on the image display unit.
  • the extraction unit obtains an average value of elasticity values of a plurality of voxels included in each region of interest, and is set based on the average value.
  • the voxel that is included in the elastic range having the upper limit value and the lower limit value and is continuously connected to the voxel located at the center coordinate and the center coordinate of each region of interest is extracted as a voxel group.
  • a volume rendering is performed on the elastic volume data of the voxel group extracted by the above or the elastic volume data excluding the voxel group to generate a three-dimensional elastic image, which is displayed on the image display unit.
  • FIG. 8 shows an example of the display image of the sixth embodiment.
  • the interface unit 43 for example, two regions of interest 126 and 127 are selected.
  • the selected coordinate calculation unit 51, the selection elasticity value calculation unit 52, and the selection volume calculation unit 53 perform calculations in the same manner as in the fifth embodiment to extract the extracted elasticity volumes 128 and 129.
  • the elastic volume rendering unit 42 renders the extracted elastic volume 128 having a small average elasticity value with reduced opacity. Thereby, a volume with a small average elastic value can be displayed slightly transparently.
  • elastic modulus, viscosity, etc. can be considered as the elastic value.
  • the opacity may be adjusted by the maximum value of the elasticity value instead of the average value of the elasticity value. Further, the opacity may be reduced when rendering an extracted elastic volume having a large average elasticity value. In this case, distortion, viscosity, etc. can be considered as the elastic value.
  • FIGS. 9 and 10 show examples of display images of the seventh embodiment.
  • the extracted elastic volume 130 was extracted.
  • the selected volume calculation unit 53 forms and outputs a volume mask 131 in which “1” is set in the voxel in which the extracted elastic volume 130 exists and “0” is set in the non-existing voxel, as shown in FIG. .
  • the elastic volume rendering unit 42 performs volume rendering including a volume that has not been extracted, and displays it as shown in FIG.
  • the operator pushes the XY plane of the three-dimensional elastic image from the cross-sectional position 133 to the cross-sectional position 134 via the interface unit 43.
  • the elastic volume rendering unit 42 sets the elastic value of the voxel included in the cross-sectional position 134 from the cross-sectional position 133 and having “0” in the volume mask 131 to “0”, as shown in FIG. 135 is displayed. This makes it possible to observe the relationship with the cross-section of the surrounding volume while leaving the volume extracted by setting the region of interest.
  • the concept of the volume mask 131 of this embodiment can be applied to editing other than removal.
  • the voxel corresponding to the position having “1” in the volume mask 131 can be edited. In other words, the extracted elastic volume data is masked and a selection volume calculation unit that outputs a masking region is provided.
  • the three-dimensional elastic image creation unit performs volume editing work only on the masking region.

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Abstract

L'invention porte sur une configuration comprenant : une unité de création de données de volume d'élasticité (40) qui crée des données de volume d'élasticité sur la base de données d'image ultrasonore qui sont acquises au moyen d'un ultrason émis vers un spécimen et reçu par un spécimen ; une interface (43) qui configure une région d'intérêt dans un espace prescrit d'un espace que les données de volume d'élasticité occupent ; une unité de calcul de volume de sélection (53) qui extrait un groupe de voxels de données de volume d'élasticité, ledit groupe de voxels comprenant une valeur de voxel dans une plage d'élasticité réglée qui est réglée sur la base d'une valeur d'élasticité d'un voxel de la région d'intérêt ; une unité de restitution par volume d'élasticité (42) qui restitue par volume soit les données de volume d'élasticité du groupe de voxels extrait, soit des données de volume excluant le groupe de voxels et génère une image d'élasticité en trois dimensions ; et un appareil d'affichage d'image (13) qui affiche l'image d'élasticité en trois dimensions générée.
PCT/JP2011/066406 2010-07-27 2011-07-20 Dispositif de diagnostic ultrasonore Ceased WO2012014739A1 (fr)

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EP11812330.6A EP2599445A1 (fr) 2010-07-27 2011-07-20 Dispositif de diagnostic ultrasonore
JP2012526442A JP5770189B2 (ja) 2010-07-27 2011-07-20 超音波診断装置
US13/809,700 US9101289B2 (en) 2010-07-27 2011-07-20 Ultrasonic diagnostic apparatus
CN201180027580.8A CN102933155B (zh) 2010-07-27 2011-07-20 超声波诊断装置

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Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2012115283A (ja) * 2010-11-29 2012-06-21 Ge Medical Systems Global Technology Co Llc 超音波診断装置及びその制御プログラム
JP2012130559A (ja) * 2010-12-22 2012-07-12 Toshiba Corp 超音波診断装置及び画像処理装置
JP2015509443A (ja) * 2012-03-09 2015-03-30 セノ メディカル インストルメンツ，インク． 光音響イメージングシステムにおける統計マッピング
JP2015522367A (ja) * 2012-07-18 2015-08-06 コーニンクレッカ フィリップス エヌ ヴェ 超音波イメージングデータを処理する方法及びシステム

Families Citing this family (14)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP2599445A1 (fr) * 2010-07-27 2013-06-05 Hitachi Medical Corporation Dispositif de diagnostic ultrasonore
US9289191B2 (en) 2011-10-12 2016-03-22 Seno Medical Instruments, Inc. System and method for acquiring optoacoustic data and producing parametric maps thereof
US11287309B2 (en) 2011-11-02 2022-03-29 Seno Medical Instruments, Inc. Optoacoustic component utilization tracking
US9730587B2 (en) 2011-11-02 2017-08-15 Seno Medical Instruments, Inc. Diagnostic simulator
US9743839B2 (en) 2011-11-02 2017-08-29 Seno Medical Instruments, Inc. Playback mode in an optoacoustic imaging system
JP5943598B2 (ja) * 2011-12-26 2016-07-05 キヤノン株式会社 被検体情報取得装置
US9311704B2 (en) * 2012-10-18 2016-04-12 Hitachi Aloka Medical, Ltd. Ultrasonic diagnosis apparatus and image display method
KR20140131808A (ko) * 2013-05-06 2014-11-14 삼성전자주식회사 초음파 영상 장치 및 그 제어 방법
US9775578B2 (en) * 2013-08-12 2017-10-03 Biosense Webster (Israel) Ltd. Unmapped region visualization
KR102096410B1 (ko) * 2014-05-02 2020-04-03 삼성전자주식회사 의료 영상 장치 및 그 제어 방법
EP3000401B1 (fr) * 2014-09-23 2022-11-09 Samsung Medison Co., Ltd. Procédé et appareil de génération d'image ultrasonore
KR102270721B1 (ko) * 2014-09-23 2021-06-30 삼성메디슨 주식회사 초음파 영상 장치 및 초음파 영상 생성 방법
JP6212160B1 (ja) * 2016-04-21 2017-10-11 株式会社日立製作所 超音波診断装置
CN110477949B (zh) * 2019-08-26 2022-11-29 东软医疗系统股份有限公司 超声成像方法、装置及超声成像设备

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH07178090A (ja) * 1993-12-24 1995-07-18 Ge Yokogawa Medical Syst Ltd 連続体識別方法および装置ならびに超音波血流表示方法および装置
JPH07299060A (ja) * 1994-05-10 1995-11-14 Toshiba Corp 画像処理装置
JP2000060853A (ja) * 1998-08-20 2000-02-29 Hitachi Medical Corp 超音波診断装置
JP2008220802A (ja) * 2007-03-15 2008-09-25 Hitachi Medical Corp 医用画像診断装置
JP2008259605A (ja) * 2007-04-11 2008-10-30 Hitachi Medical Corp 超音波診断装置
WO2010026823A1 (fr) * 2008-09-08 2010-03-11 株式会社 日立メディコ Appareil de diagnostic par ultrasons et procédé d'affichage d'image par ultrasons

Family Cites Families (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1762180B1 (fr) * 2004-06-09 2015-04-15 Hitachi Medical Corporation Procédé d'affichage d'image élastique et dispositif ultrasonographique
KR100752333B1 (ko) * 2005-01-24 2007-08-28 주식회사 메디슨 3차원 초음파 도플러 이미지의 화질 개선 방법
JP2006218210A (ja) * 2005-02-14 2006-08-24 Toshiba Corp 超音波診断装置、超音波画像生成プログラム及び超音波画像生成方法
WO2010020921A2 (fr) * 2008-08-20 2010-02-25 Koninklijke Philips Electronics N.V. Occultation de régions d’une image
JP2010148828A (ja) * 2008-12-26 2010-07-08 Toshiba Corp 超音波診断装置及び超音波診断装置の制御プログラム
EP2599445A1 (fr) * 2010-07-27 2013-06-05 Hitachi Medical Corporation Dispositif de diagnostic ultrasonore

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH07178090A (ja) * 1993-12-24 1995-07-18 Ge Yokogawa Medical Syst Ltd 連続体識別方法および装置ならびに超音波血流表示方法および装置
JPH07299060A (ja) * 1994-05-10 1995-11-14 Toshiba Corp 画像処理装置
JP2000060853A (ja) * 1998-08-20 2000-02-29 Hitachi Medical Corp 超音波診断装置
JP2008220802A (ja) * 2007-03-15 2008-09-25 Hitachi Medical Corp 医用画像診断装置
JP2008259605A (ja) * 2007-04-11 2008-10-30 Hitachi Medical Corp 超音波診断装置
WO2010026823A1 (fr) * 2008-09-08 2010-03-11 株式会社 日立メディコ Appareil de diagnostic par ultrasons et procédé d'affichage d'image par ultrasons

Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2012115283A (ja) * 2010-11-29 2012-06-21 Ge Medical Systems Global Technology Co Llc 超音波診断装置及びその制御プログラム
JP2012130559A (ja) * 2010-12-22 2012-07-12 Toshiba Corp 超音波診断装置及び画像処理装置
JP2015509443A (ja) * 2012-03-09 2015-03-30 セノ メディカル インストルメンツ，インク． 光音響イメージングシステムにおける統計マッピング
JP2018149362A (ja) * 2012-03-09 2018-09-27 セノ メディカル インストルメンツ，インク． 光音響イメージングシステムにおける統計マッピング
JP2015522367A (ja) * 2012-07-18 2015-08-06 コーニンクレッカ フィリップス エヌ ヴェ 超音波イメージングデータを処理する方法及びシステム

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JPWO2012014739A1 (ja) 2013-09-12
CN102933155A (zh) 2013-02-13
CN102933155B (zh) 2015-07-15

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